US7458372B2 - Inhalation therapy device - Google Patents

Inhalation therapy device Download PDF

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US7458372B2
US7458372B2 US10/533,430 US53343005A US7458372B2 US 7458372 B2 US7458372 B2 US 7458372B2 US 53343005 A US53343005 A US 53343005A US 7458372 B2 US7458372 B2 US 7458372B2
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liquid
inhalation therapy
membrane
therapy device
oscillation generating
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US20060102172A1 (en
Inventor
Franz Feiner
Markus Borgschulte
Wolfgang Achtzehner
Eduard Kunschir
Joseph Lass
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PARI Pharma GmbH
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PARI Pharma GmbH
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M15/00—Inhalators
    • A61M15/0065—Inhalators with dosage or measuring devices
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M15/00—Inhalators
    • A61M15/0065—Inhalators with dosage or measuring devices
    • A61M15/0068—Indicating or counting the number of dispensed doses or of remaining doses
    • A61M15/008—Electronic counters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M15/00—Inhalators
    • A61M15/0085—Inhalators using ultrasonics
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B05—SPRAYING OR ATOMISING IN GENERAL; APPLYING FLUENT MATERIALS TO SURFACES, IN GENERAL
    • B05B—SPRAYING APPARATUS; ATOMISING APPARATUS; NOZZLES
    • B05B12/00—Arrangements for controlling delivery; Arrangements for controlling the spray area
    • B05B12/08—Arrangements for controlling delivery; Arrangements for controlling the spray area responsive to condition of liquid or other fluent material to be discharged, of ambient medium or of target ; responsive to condition of spray devices or of supply means, e.g. pipes, pumps or their drive means
    • B05B12/081—Arrangements for controlling delivery; Arrangements for controlling the spray area responsive to condition of liquid or other fluent material to be discharged, of ambient medium or of target ; responsive to condition of spray devices or of supply means, e.g. pipes, pumps or their drive means responsive to the weight of a reservoir or container for liquid or other fluent material; responsive to level or volume of liquid or other fluent material in a reservoir or container
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B05—SPRAYING OR ATOMISING IN GENERAL; APPLYING FLUENT MATERIALS TO SURFACES, IN GENERAL
    • B05B—SPRAYING APPARATUS; ATOMISING APPARATUS; NOZZLES
    • B05B17/00—Apparatus for spraying or atomising liquids or other fluent materials, not covered by the preceding groups
    • B05B17/04—Apparatus for spraying or atomising liquids or other fluent materials, not covered by the preceding groups operating with special methods
    • B05B17/06—Apparatus for spraying or atomising liquids or other fluent materials, not covered by the preceding groups operating with special methods using ultrasonic or other kinds of vibrations
    • B05B17/0607—Apparatus for spraying or atomising liquids or other fluent materials, not covered by the preceding groups operating with special methods using ultrasonic or other kinds of vibrations generated by electrical means, e.g. piezoelectric transducers
    • B05B17/0638—Apparatus for spraying or atomising liquids or other fluent materials, not covered by the preceding groups operating with special methods using ultrasonic or other kinds of vibrations generated by electrical means, e.g. piezoelectric transducers spray being produced by discharging the liquid or other fluent material through a plate comprising a plurality of orifices
    • B05B17/0646—Vibrating plates, i.e. plates being directly subjected to the vibrations, e.g. having a piezoelectric transducer attached thereto
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B05—SPRAYING OR ATOMISING IN GENERAL; APPLYING FLUENT MATERIALS TO SURFACES, IN GENERAL
    • B05B—SPRAYING APPARATUS; ATOMISING APPARATUS; NOZZLES
    • B05B17/00—Apparatus for spraying or atomising liquids or other fluent materials, not covered by the preceding groups
    • B05B17/04—Apparatus for spraying or atomising liquids or other fluent materials, not covered by the preceding groups operating with special methods
    • B05B17/06—Apparatus for spraying or atomising liquids or other fluent materials, not covered by the preceding groups operating with special methods using ultrasonic or other kinds of vibrations
    • B05B17/0607—Apparatus for spraying or atomising liquids or other fluent materials, not covered by the preceding groups operating with special methods using ultrasonic or other kinds of vibrations generated by electrical means, e.g. piezoelectric transducers
    • B05B17/0653—Details
    • B05B17/0669—Excitation frequencies
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3375—Acoustical, e.g. ultrasonic, measuring means
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3379—Masses, volumes, levels of fluids in reservoirs, flow rates
    • A61M2205/3386—Low level detectors

Definitions

  • the invention relates to inhalation therapy devices having an oscillatable membrane for nebulising a liquid.
  • the aerosol membrane generator described therein comprises a cylindrical liquid storage container which is delimited at one end face by a membrane having the shape of a circular disc.
  • DE 199 53 317 C1 furthermore describes an oscillation generator, for example a piezo crystal, which surrounds the membrane in a circular manner and is connected thereto such that the membrane can be caused to oscillate by means of the oscillation generator and an electric drive circuit.
  • an oscillation generator for example a piezo crystal, which surrounds the membrane in a circular manner and is connected thereto such that the membrane can be caused to oscillate by means of the oscillation generator and an electric drive circuit.
  • the liquid abutting the membrane on the one side is conveyed through holes in the oscillating membrane to the other side of said membrane and is emitted on this side into the mixing chamber as an aerosol.
  • an ultrasonic liquid nebuliser having a piezo crystal which is caused to oscillate electrically by an oscillator circuit, said oscillator circuit being supplied by a power supply device.
  • DE 295 01 569 describes an oscillator circuit which comprises a current limiting circuit and which is connected with an electronic temperature limiting circuit that compares a temperature-dependant electric signal occurring at the piezo crystal in a threshold circuit, the comparison signal of which activates a bistable circuit which blocks the oscillator when a limiting temperature in the piezo crystal is reached.
  • DE 295 01 569 is thereby directed at a protective mechanism for an ultrasonic liquid nebuliser in which the piezo crystal itself causes the liquid to oscillate and is in contact with a comparatively large amount of liquid.
  • the liquid nebuliser described in DE 295 01 569 must furthermore accordingly use large currents in order to cause the large amount of liquid to oscillate.
  • Constant contact between the piezo crystal and the liquid is necessary owing to these large currents and the resulting large temperature differences in order to prevent destruction of the piezo crystal. If there is no longer any liquid present, the piezo crystal heats up very quickly and is destroyed if the oscillating circuit driving the nebuliser is not switched off immediately.
  • inhalation nebulisers of the type described at the beginning of this document, i.e. in inhalation nebulisers having membrane aerosol generators, and therefore only comparatively small temperature differences occur.
  • inhalation nebulisers the lack of liquid does not directly lead to heat-related damage to the piezo-electric elements.
  • a membrane inhalation nebuliser runs without a load, this can, on rare occasions, cause the membrane to break.
  • inhalation nebulisers having a membrane generator it is also necessary in inhalation nebulisers having a membrane generator to reliably detect the presence of a liquid to be nebulised. This is because, on the one hand, the basis for a very high dosage accuracy is thereby created and, on the other hand, it is possible to reliably indicate the end of a therapy session to the patient. Furthermore, by immediately disconnecting the inhalation therapy device, it is possible, for example, to save a battery.
  • the object of the present invention is therefore to configure an inhalation therapy device having a membrane aerosol generator and a corresponding method such that it is possible to reliably detect whether or not a liquid is present in the liquid reservoir of the inhalation therapy device.
  • Such an inhalation therapy device comprises an oscillatable membrane for nebulising a liquid, an oscillation generating device which has at least one connecting means for supplying an activation signal and by means of which the membrane is caused to oscillate when the activation signal is supplied such that a liquid disposed on one side of the membrane is nebulised through said membrane and is present on the other side of the membrane as an aerosol, and a control means from which an activation signal can be supplied to the at least one connecting means of the oscillation generating device such that the oscillation generating device causes the membrane to oscillate, characterised in that a detection device is provided which detects at least one electric parameter of the oscillatable structure comprising the membrane and the oscillation generating device and which determines the presence of a liquid to be nebulised based on the at least one parameter.
  • the object is furthermore solved by an inhalation therapy method.
  • Such an inhalation therapy method for an inhalation therapy device comprises the following steps:
  • the invention enables a greater dosage accuracy of the medicament for the patient, allows the patient to concentrate better on the therapy and increases the user-friendliness of the inhalation therapy device, not least owing to a longer running time during battery operation.
  • detection of the at least one electric parameter means that the battery capacity can be saved and that it can be determined whether there is a bad contact in the inhalation therapy device or whether droplets have formed on the membrane, which affects the nebulising properties of the device.
  • a worse TOR (Total Output Rate) is furthermore also recognised.
  • the accuracy of the dose of the inhalation substance can be improved by the invention and the patient can concentrate better on the therapy, which leads to improved treatment success.
  • the inhalation therapy device recognise both phenomena since both droplet formation and clogging of the membrane change the at least one detected electric parameter of the oscillatable structure in a characteristic manner. Countermeasures (e.g. switching off the device) can thereby be taken in good time.
  • FIG. 1 shows a schematic representation of an inhalation device according to a first embodiment example
  • FIG. 2 shows a flow diagram which graphically represents a method for determining the presence of liquid in the inhalation device according to a first embodiment example
  • FIG. 3 shows a schematic representation of an inhalation therapy device according to a second embodiment example
  • FIG. 4 shows a flow diagram which graphically represents a method for determining the presence of liquid in the inhalation device according to a second embodiment example
  • FIG. 5 shows an example of the progression over time of a measuring curve of a detected electric parameter when using two different oscillation frequencies for the membrane according to a second embodiment example.
  • FIGS. 1 and 2 the invention will now be explained in more detail below by means of a first embodiment.
  • FIG. 1 shows an inhalation therapy device according to the invention, in which in a nebuliser unit A, a liquid ( 3 ) stored in a liquid reservoir ( 2 ) is nebulised by means of a membrane ( 1 ) into a nebulisation cavity ( 4 ).
  • Nebulisation then occurs when the membrane ( 1 ) is caused to oscillate.
  • the membrane ( 1 ) is attached to a support unit ( 6 ) which supports the membrane ( 1 ) and to which an electromechanical transducer unit ( 7 ), for example a piezo element, is also attached.
  • the membrane ( 1 ), the support unit ( 6 ) and the electromechanical transducer unit ( 7 ) are configured in a rotationally symmetrical manner in the embodiment described here and together form an oscillatable structure.
  • An activation signal of a control means ( 10 ) can be supplied to the electromechanical transducer unit ( 7 ) via connecting lines ( 8 , 9 ), said control means being accommodated in a separate control unit B in the embodiment described here.
  • the activation signal is supplied, the oscillatable structure ( 1 , 6 , 7 ) is caused to oscillate and the liquid ( 3 ) is nebulised through the membrane ( 1 ).
  • a patient can inhale the aerosol provided in the nebulisation cavity ( 4 ) at the mouthpiece ( 11 ) of the nebuliser. So that a sufficient amount of air is supplied, one or more air holes ( 12 ) are provided in the housing of the nebuliser, through which ambient air can enter into the cavity ( 4 ) during inhalation and out of which the air inhaled by the patient can exit from the cavity ( 4 ) during exhalation.
  • the oscillatable structure ( 1 , 6 , 7 ) displays very specific characteristics during nebulisation and during operation without liquid, which are reflected in the electric parameters of the oscillatable structure.
  • the operating states with and without liquid on the membrane can be reliably determined by means of these electric parameters.
  • Current consumption (current), power consumption (power) and the current/voltage phase shift (phase position) are particularly suitable as electric parameters.
  • a detection device ( 13 ) is provided according to the invention, which is configured and is connected with the oscillatable structure ( 1 , 6 , 7 ) and/or the control means ( 10 ) such that the at least one electric parameter is supplied to the detection device ( 13 ).
  • the connecting lines ( 8 , 9 ) are configured such that during operation of the control unit ( 10 ), at least one electric parameter of the oscillatable structure ( 1 , 6 , 7 ) is transmitted to the detection device ( 13 ) via the connecting lines ( 8 , 9 ) and can be detected thereby.
  • the invention is based on the surprising possibility of being able to draw conclusions with regard to the operating state as a result of the detection of at least one electric parameter of the oscillatable structure ( 1 , 6 , 7 ) (e.g. voltage tap, current consumption or the current/voltage phase position at the piezo crystal of the membrane) owing to the characteristics of the oscillatable structure ( 1 , 6 , 7 ) and it can thereby be determined whether or not liquid ( 3 ) is still present in the liquid reservoir ( 2 ).
  • at least one electric parameter of the oscillatable structure ( 1 , 6 , 7 ) e.g. voltage tap, current consumption or the current/voltage phase position at the piezo crystal of the membrane
  • Detection of the at least one electric parameter of the oscillatable structure ( 1 , 6 , 7 ) by the detection device ( 13 ) can occur continuously or at discrete time intervals.
  • Determination of the operating state i.e. determination of whether liquid is present or not, preferably occurs in the detection device ( 13 ) by comparing the detected value of the at least one parameter with a value for this parameter stored in said detection device.
  • the detection device ( 13 ) comprises, for example, a memory ( 13 a ) for this purpose.
  • the detection device ( 13 ) determines that there is no more liquid ( 3 ) stored in the liquid reservoir ( 2 ), the detection device ( 13 ) then emits, in a preferred embodiment, a signal to the control means ( 10 ), which in turn automatically stops the supply of activation signals to the oscillatable structure ( 1 , 6 , 7 ), i.e. automatically switches off the inhalation therapy device.
  • the detection device (additionally) emits an optical or audio signal to indicate to the patient that the inhalation therapy device has consumed the stored liquid ( 3 ) in the liquid reservoir ( 2 ), which signals the end of the therapy session to the patient.
  • the patient can then switch off the inhalation therapy device if automatic switching off is not provided in addition to the optical/audio signal.
  • the inhalation therapy device comprises a signal emitting means ( 14 ) for emitting the audio/optical signal, which is connected with the detection device ( 13 ) (or alternatively the control means).
  • the audio signal emitted for this purpose can be a short sound signal of 0.5 to 2 seconds in length.
  • These audio signals are, however, not just restricted to notes, rather sound sequences or recorded or synthesised voice signals can also be used.
  • FIG. 2 shows a flow diagram, by means of which a possible course of a therapy session will now be described.
  • step S 1 By switching on the inhalation therapy device (step S 1 ), activation signals are supplied to the oscillatable structure (step S 2 ). Immediately afterwards, the detection device ( 13 ) verifies whether the initial conditions for a therapy session exist, i.e. it determines whether liquid ( 3 ) is present in the liquid reservoir ( 2 ).
  • the detection device ( 13 ) detects at least one electric parameter of the oscillatable structure ( 1 , 6 , 7 ) (step S 3 ) and determines, based on the detected value of the at least one electric parameter, whether liquid is present or not (step S 4 ).
  • the detection device ( 13 ) reverts, for example, to empirically determined values for the detected electric parameter, which are stored in a suitable manner in the detection device, for example in the semiconductor memory ( 13 a ) shown in FIG. 1 , or uses a value of the at least one parameter which was detected in a previous cycle of the loop (see below). This value is stored in a suitable form by the detection deivce ( 13 ) for this purpose, for example in the semiconductor memory ( 13 a ).
  • step S 5 If the presence of liquid is determined by a comparison of the values (step S 5 ), the activation signal continues to be supplied to the oscillatable structure ( 1 , 6 , 7 ); the control sequence then returns to step S 2 .
  • step S 5 If, on the other hand, it is determined in step S 5 that no liquid is present, supply of the activation signal to the oscillatable structure ( 1 , 6 , 7 ) is immediately stopped again (step S 6 ).
  • An optical/audio signal can be additionally or alternatively emitted (step S 6 ).
  • the loop of steps S 2 to S 5 is performed continuously or at regular intervals (discrete time steps) in order to verify the presence of liquid during the therapy session and, if necessary to stop the supply of the activation signal to the oscillatable structure, and thus to stop nebulisation.
  • FIGS. 3 to 5 A second embodiment example of the invention will now be explained by means of FIGS. 3 to 5 .
  • FIG. 3 shows a second embodiment example of an inhalation therapy device, in which at least two different oscillation frequencies for the membrane are generated and are alternatingly supplied to the membrane.
  • the first frequency f 1 is the activation frequency which is supplied to the oscillatable structure ( 1 , 6 , 7 ) in order to cause the membrane to oscillate and to nebulise the liquid.
  • the second frequency f 2 on the other hand is a frequency used for determining the operating state of the oscillatable structure ( 1 , 6 , 7 ).
  • the time periods in which the second frequency f 2 is supplied to the oscillatable structure ( 1 , 6 , 7 ) are typically much shorter than the time periods in which the first frequency f 1 is supplied. This is because the second frequency f 2 is supplied for measuring purposes and may only disturb the generation of the aerosol to the smallest extent possible.
  • control unit ( 10 ) comprises, for example, an oscillator ( 20 ) for this purpose in this second embodiment, which can generate at least two different oscillation frequencies (f 1 , f 2 ) for the membrane ( 1 ).
  • a switching means ( 21 ) switches the oscillator ( 20 ) of the control unit ( 10 ) between the normal operating frequency f 1 and the measuring frequency f 2 at predetermined times, the inhalation therapy device nebulising the available liquid during the intervals in which the normal operating frequency f 2 is used.
  • the detection unit ( 13 ) stores the detected values of the at least one electric parameter which were detected when using the measuring frequency f 2 in order to be able to analyse these measured values also over a longer period of time.
  • Determination of the operating state i.e. determination of whether liquid is present or not, then occurs in the detection device ( 13 ) either by comparing a value of the at least one parameter that was detected during the normal operating frequency f 1 with a value for this parameter that is stored in the detection device (the detection device ( 13 ) comprises, for example, a memory ( 13 a ) for this purpose), or by evaluating values of an electric parameter that were recorded when using the measuring frequency f 2 .
  • the operating state can, of course, also be determined by using values of both sets of detected parameters.
  • the detection device ( 13 ) determines that no more liquid ( 3 ) is stored in the liquid reservoir ( 2 ), the detection device ( 13 ) then, in a preferred embodiment, emits a signal to the control means ( 10 ), which in turn automatically stops the supply of activation signals to the oscillatable structure ( 1 , 6 , 7 ), i.e. automatically switches off the inhalation therapy device.
  • FIG. 4 shows a flow diagram, by means of which a possible course of a therapy session according to the second embodiment will now be described.
  • step S 1 By switching on the inhalation therapy device (step S 1 ), activation signals having a normal operating frequency f 1 are supplied to the oscillatable structure (step S 2 ). Immediately afterwards, the detection device ( 13 ) verifies whether the initial conditions for a therapy session exist, i.e. it determines whether liquid ( 3 ) is present in the liquid reservoir ( 2 ).
  • the detection device ( 13 ) detects at least one electric parameter of the oscillatable structure ( 1 , 6 , 7 ) when using the normal operating frequency f 1 (step S 3 ) and determines, based on the detected value of the at least one electric parameter, whether liquid is present or not (step S 4 ).
  • the detection device ( 13 ) reverts, for example, to empirically determined values for the detected electric parameter, which are stored in a suitable manner in the detection device, for example in the semiconductor memory ( 13 a ) as shown in FIG. 3 .
  • step S 5 If the presence of liquid is determined (step S 5 ), the activation signal continues to be supplied to the oscillatable structure ( 1 , 6 , 7 ); the control sequence then returns to step S 2 .
  • step S 5 If, on the other hand, it is determined in step S 5 that no liquid is present, supply of the activation signal to the oscillatable structure ( 1 , 6 , 7 ) is immediately stopped again (step S 6 ).
  • An optical/audio signal can be additionally or alternatively emitted (step S 6 ).
  • the loop of steps S 2 to S 5 is performed continuously or at regular intervals (discrete time steps) in order to verify the presence of liquid during the therapy session and, if necessary to stop the supply of the activation signal to the oscillatable structure and thus nebulisation.
  • Switching between the normal operating frequency f 1 and the measuring frequency f 2 is thereby carried out at predetermined intervals.
  • the length of the time intervals during which the measuring frequency f 2 is used are selected such that the nebulising operation is not disturbed.
  • the time intervals of the measuring frequency are typically smaller by at least a factor of 10.
  • the detection device ( 13 ) detects at least one electric parameter of the oscillatable structure ( 1 , 6 , 7 ) during use of the normal operating frequency f 1 (step S 3 ) or the measuring frequency f 2 (step 3 ′) and determines, based on the detected values of the at least one electric parameter, whether liquid is present or not (step S 4 ).
  • the detection device ( 13 ) reverts, as regards the values detected using the normal operating frequency f 1 (step 3 ), either to empirically determined values for the detected electric parameter, which are stored in a suitable manner in the detection device, for example in the semiconductor memory ( 13 a ) as shown in FIG. 3 , or uses a value of the at least one parameter which was detected in a previous cycle of the loop. This value was stored for this purpose in a suitable form by the detection device ( 13 ), for example in the semiconductor memory ( 13 a ).
  • the detection device ( 13 ) evaluates the detected values of the at least one electric parameter of the oscillatable structure ( 1 , 6 , 7 ) that were determined during use of the measuring frequency f 2 and were stored in the memory ( 13 b ) (step 3 ′) either just like the other measured values or, preferably, over a longer period of time (step 4 ).
  • the decision as to whether or not liquid is present can be based in this embodiment example on both types of detected values of the electric parameters. This increases the certitude of the accuracy of the determination of whether or not liquid is present. Furthermore, by observing the course of the measuring curve over a longer period of time, the reliability of the determination of whether or not liquid is present can be further increased.
  • the invention is, however, not restricted to the use of two frequencies. Several frequencies can be used for the described device.
  • FIG. 5 shows an example of the progression over time of one of the detected electric parameters when two different frequencies are used for the membrane oscillations.
  • FIG. 5 An example measuring curve can be seen in FIG. 5 , which shows the progression of the detected values of the at least one electric parameter of the oscillatable structure ( 1 , 6 , 7 ) according to the second embodiment example.
  • the measured value in the example measuring curve is the current consumption of the oscillatable structure ( 1 , 6 , 7 ) in mA.
  • the progression over the time period of 0 to approximately 17 seconds can be attributed to the switching-on process and can be disregarded.
  • the short time intervals in which an activation signal having the measuring frequency f 2 is applied to the oscillatable structure ( 1 , 6 , 7 ) can also be recognised in FIG. 5 .
  • These time intervals correspond to the peaks recognisable in FIG. 5 , and it is also clear that these time intervals are shorter than the time intervals between the peaks in which the operating frequency f 1 is used.
  • the measured values detected for the operating frequency f 1 are in a very narrow range of approximately 1.6 mA. After the 85 th second, the measuring curve of the values decreases to approximately 0.9 mA for the operating frequency f 1 . After approximately the 97 th second, the measured values are again essentially constant.
  • the peak values are interesting, which increase over the entire progression of the curve.
  • the peak values proceed along a straight line with a first gradient; in the period after the 95 th second, the peak values of the measured values for the measuring frequency f 2 proceed along a straight line with a second gradient which is greater than the first gradient.
  • This change in gradient is a clearly recognisable sign that liquid is lacking on the membrane or on the oscillatable structure ( 1 , 6 , 7 ) of the inhalation therapy device.
  • the second embodiment example of the inhalation therapy device has two measuring curve progressions, using which the lack of liquid can be determined. This is because, on the one hand, the measuring curve of the values for the operating frequency f 1 declines when the liquid has been consumed and, on the other hand, the rate of increase of the peak values of the values determined for measuring frequency f 2 changes.
  • the measuring curve shown in FIG. 5 is just an example and can change for different designs of the inhalation therapy device.
  • the values and time periods specified can differ depending on the specific configuration of the device.

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  • Engineering & Computer Science (AREA)
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  • Special Spraying Apparatus (AREA)
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US10/533,430 2002-10-30 2003-10-30 Inhalation therapy device Active 2024-11-18 US7458372B2 (en)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
DE10250625A DE10250625A1 (de) 2002-10-30 2002-10-30 Inhalationstherapievorrichtung
DE10250625.6 2002-10-30
PCT/EP2003/012076 WO2004039442A1 (fr) 2002-10-30 2003-10-30 Appareil de therapie par inhalation

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US20060102172A1 US20060102172A1 (en) 2006-05-18
US7458372B2 true US7458372B2 (en) 2008-12-02

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US (1) US7458372B2 (fr)
EP (1) EP1558315B1 (fr)
AT (1) ATE453424T1 (fr)
DE (2) DE10250625A1 (fr)
WO (1) WO2004039442A1 (fr)

Cited By (19)

* Cited by examiner, † Cited by third party
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US20080308096A1 (en) * 2005-02-11 2008-12-18 Pari Pharma Gmbh Aerosol Generating Device and Inhalation Therapy Unit Provided with This Device
US8061352B2 (en) 1996-02-13 2011-11-22 Trudell Medical International Aerosol delivery apparatus and method
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US8061352B2 (en) 1996-02-13 2011-11-22 Trudell Medical International Aerosol delivery apparatus and method
US10881816B2 (en) 2002-05-21 2021-01-05 Trudell Medical International Medication delivery apparatus and system and methods for the use and assembly thereof
US8074642B2 (en) 2002-05-21 2011-12-13 Trudell Medical International Visual indicator for an aerosol medication delivery apparatus and system
US8550067B2 (en) 2002-05-21 2013-10-08 Trudell Medical International Visual indicator for an aerosol medication delivery apparatus and system
US9700689B2 (en) 2002-05-21 2017-07-11 Trudell Medical International Medication delivery apparatus and system and methods for the use and assembly thereof
US9814849B2 (en) 2002-05-21 2017-11-14 Trudell Medical International Medication delivery apparatus and system and methods for the use and assembly thereof
US20130074832A1 (en) * 2005-02-11 2013-03-28 Pari Pharma Gmbh Aerosol generating means for inhalation therapy devices
US20080308096A1 (en) * 2005-02-11 2008-12-18 Pari Pharma Gmbh Aerosol Generating Device and Inhalation Therapy Unit Provided with This Device
US9016272B2 (en) * 2005-02-11 2015-04-28 Pari Pharma Gmbh Aerosol generating means for inhalation therapy devices
US9027548B2 (en) 2005-02-11 2015-05-12 Pari Pharma Gmbh Aerosol generating device and inhalation therapy unit provided with this device
US10328071B2 (en) 2005-12-08 2019-06-25 Insmed Incorporated Lipid-based compositions of antiinfectives for treating pulmonary infections and methods of use thereof
US10064882B2 (en) 2007-05-07 2018-09-04 Insmed Incorporated Methods of treating pulmonary disorders with liposomal amikacin formulations
US9272101B2 (en) 2010-01-19 2016-03-01 Nektar Therapeutics Identifying dry nebulizer elements
CN103153315A (zh) * 2010-10-12 2013-06-12 印斯拜尔药品股份有限公司 用吸入地纽福索治疗囊性纤维化的方法
US9566234B2 (en) 2012-05-21 2017-02-14 Insmed Incorporated Systems for treating pulmonary infections
US10124066B2 (en) 2012-11-29 2018-11-13 Insmed Incorporated Stabilized vancomycin formulations
US10471149B2 (en) 2012-11-29 2019-11-12 Insmed Incorporated Stabilized vancomycin formulations
US10398719B2 (en) 2014-05-15 2019-09-03 Insmed Incorporated Methods for treating pulmonary non-tuberculous mycobacterial infections
US11446318B2 (en) 2014-05-15 2022-09-20 Insmed Incorporated Methods for treating pulmonary non-tuberculous mycobacterial infections
US10238675B2 (en) 2014-05-15 2019-03-26 Insmed Incorporated Methods for treating pulmonary non-tuberculous mycobacterial infections
US10588918B2 (en) 2014-05-15 2020-03-17 Insmed Incorporated Methods for treating pulmonary non-tuberculous mycobacterial infections
US10751355B2 (en) 2014-05-15 2020-08-25 Insmed Incorporated Methods for treating pulmonary non-tuberculous mycobacterial infections
US12016873B2 (en) 2014-05-15 2024-06-25 Insmed Incorporated Methods for treating pulmonary non-tuberculous mycobacterial infections
US10828314B2 (en) 2014-05-15 2020-11-10 Insmed Incorporated Methods for treating pulmonary non-tuberculous mycobacterial infections
US10251900B2 (en) 2014-05-15 2019-04-09 Insmed Incorporated Methods for treating pulmonary non-tuberculous mycobacterial infections
US9895385B2 (en) 2014-05-15 2018-02-20 Insmed Incorporated Methods for treating pulmonary non-tuberculous mycobacterial infections
US11395830B2 (en) 2014-05-15 2022-07-26 Insmed Incorporated Methods for treating pulmonary non-tuberculous mycobacterial infections
US10850050B2 (en) 2016-05-19 2020-12-01 Trudell Medical International Smart valved holding chamber
US11975140B2 (en) 2016-05-19 2024-05-07 Trudell Medical International Medication delivery system with mask
US11839716B2 (en) 2016-07-08 2023-12-12 Trudell Medical International Smart oscillating positive expiratory pressure device
US12097320B2 (en) 2016-07-08 2024-09-24 Trudell Medical International Inc. Nebulizer apparatus and method
US10786638B2 (en) 2016-07-08 2020-09-29 Trudell Medical International Nebulizer apparatus and method
US11497867B2 (en) 2016-12-09 2022-11-15 Trudell Medical International Smart nebulizer
US11964185B2 (en) 2018-01-04 2024-04-23 Trudell Medical International Smart oscillating positive expiratory pressure device
US11666801B2 (en) 2018-01-04 2023-06-06 Trudell Medical International Smart oscillating positive expiratory pressure device
US11571386B2 (en) 2018-03-30 2023-02-07 Insmed Incorporated Methods for continuous manufacture of liposomal drug products
US11712175B2 (en) 2019-08-27 2023-08-01 Trudell Medical International Smart oscillating positive expiratory pressure device with feedback indicia
US12011535B2 (en) 2019-10-20 2024-06-18 Qnovia, Inc. Electronic devices and liquids for aerosolizing and inhaling therewith

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EP1558315B1 (fr) 2009-12-30
WO2004039442A1 (fr) 2004-05-13
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DE50312299D1 (de) 2010-02-11
ATE453424T1 (de) 2010-01-15
EP1558315A1 (fr) 2005-08-03

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